US6603552B1 - Portable system for detecting skin abnormalities based on characteristic autofluorescence - Google Patents
Portable system for detecting skin abnormalities based on characteristic autofluorescence Download PDFInfo
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- US6603552B1 US6603552B1 US09/469,562 US46956299A US6603552B1 US 6603552 B1 US6603552 B1 US 6603552B1 US 46956299 A US46956299 A US 46956299A US 6603552 B1 US6603552 B1 US 6603552B1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/44—Detecting, measuring or recording for evaluating the integumentary system, e.g. skin, hair or nails
- A61B5/441—Skin evaluation, e.g. for skin disorder diagnosis
- A61B5/444—Evaluating skin marks, e.g. mole, nevi, tumour, scar
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0071—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence by measuring fluorescence emission
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- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0088—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for oral or dental tissue
Definitions
- the present invention relates to the detection of skin abnormalities and, more particularly, to the detection of cancerous or precancerous skin tissue using autofluorescence.
- One technique that can aid a physician in the detection of cancerous or pre-cancerous lesions is based on the difference in autofluorescence light produced by healthy and non-healthy tissue. All tissue will fluoresce or produce light within a well-defined range of wavelengths when excited. It is known that the autofluorescence light produced by healthy tissue has a spectral profile that differs from that produced by non-healthy tissue. A number of research groups have exploited this difference in the spectral profile by recording the wavelength spectrum of a single point. Although this provides interesting data, it is clinically difficult to use.
- the present invention is a lightweight, hand-held skin abnormality detection imaging system including a source of excitation light which causes tissue under examination to produce autofluorescence light.
- the autofluorescence light generated from the tissue under examination along with reference light is directed to a pair of optical channels that produce an image of the tissue under examination.
- An optical combiner which preferably comprises a dichroic mirror, superimposes the images of the tissue to be viewed by a user.
- the autofluorescence light received in one channel has a wavelength selected such that the autofluorescence intensity for healthy tissue differs from the autofluorescence intensity produced for diseased or suspect tissue.
- the reference light comprises autofluorescence light, wherein the autofluorescence intensity for diseased tissue is substantially similar to the autofluorescence intensity for healthy tissue.
- the reference light comprises reflected excitation light.
- the reference light comprises light having wavelengths that differ from the wavelengths of the excitation light.
- the combined superimposed output images may be viewed by a user or may be captured by an analog or digital camera.
- these embodiments can all be implemented with monocular or binocular viewing.
- FIG. 1 is a schematic block diagram of a first embodiment of a skin abnormality detection system according to the present invention that detects abnormalities by providing a monocular, false color view of the skin based on two detection wavelength bands of autofluorescence light;
- FIG. 2 is an example of a combined color view produced by the present invention using a blue excitation filter, a first autofluorescence optical channel with a green emission filter and a green phosphor screen and a second autofluorescence optical channel with a red emission filter and red phosphor screen;
- FIG. 3 is a schematic block diagram of another embodiment of a skin abnormality detection system according to the present invention that detects abnormalities by providing a binocular, false color view of the skin based on two detection wavelengths of autofluorescence light;
- FIG. 4 is a schematic block diagram of yet another embodiment of a skin abnormality detection system according to the present invention that detects abnormalities by providing a camera which captures a false color image of the skin based on two detection wavelengths of autofluorescence light.
- the present invention is a lightweight, hand-held system for detecting skin abnormalities based on the differences in autofluorescence light produced by healthy and diseased tissue.
- a skin abnormality detection system 5 is made up of seven major subsystems: a light source 10 that produces excitation light that will cause a tissue sample 12 under examination to produce characteristic autofluorescence light.
- An optical splitter 13 divides the fluorescence light received from the tissue sample 12 into two beams of different wavelengths. The first beam is directed into a first optical channel 14 that collects, amplifies, and images the light in one fluorescence wavelength band, and a second beam is directed into a second optical channel 15 that collects, amplifies, and images the light in a second fluorescence wavelength band.
- An optical combiner 16 combines the images from the two optical channels 14 and 15 into one and presents the combined image the user's eye 19 .
- the system 10 includes a control module 17 , and a power source 18 .
- the system described above is a monocular viewer that produces a combined false color image that is made up of images from two fluorescence wavelength bands.
- the power source 18 could be batteries or the AC line. In the preferred embodiment battery power is utilized for portability.
- the light source 10 provides light of the required characteristics for exciting the tissue fluorescence. It consists of a power supply 21 , which is controlled by the control module 27 and which receives electrical power from power source 18 .
- the power supply outputs electrical power of the appropriate characteristics to operate a lamp 22 .
- the lamp which may be a xenon flash lamp, produces a broad spectrum output of visible light (e.g. white light).
- the light is formed into a beam which uniformly illuminates the tissue 12 by a reflector 23 and the combination of image forming elements 24 and 25 (e.g. lenses). A region of collimated light is produced between the two lenses.
- the region of collimated light provides optimal conditions for the placement of an optical band pass filter, excitation filter 26 , designed for incident light to be perpendicular to filter's surface.
- the excitation filter characteristics are preferably selected such that the filter passes light of wavelengths utilized to excite fluorescence (typically 400 nm to 450 nm) and blocks light of other wavelengths.
- the blocking by the filter in the wavelength bands where fluorescence is detected must be very good (i.e. in those bands, less than 1 in 10 5 of the light from the lamp should be able to pass through the filter).
- the lamp 22 is operated in a pulsed mode similar to a camera flash; however, it could be on continuously.
- the advantages of operating in the pulsed mode are that it allows the system to be utilized in an undarkened room and the power required is reduced so battery operation is possible.
- the intensity and duration of the light (when pulsed) are controlled by the control module 17 as a means of adjusting the brightness of the image as detected by the user's eye 19 .
- the result of illuminating the tissue 12 with excitation light is the emission of characteristic autofluorescence light 31 by the tissue. If the excitation light is in the blue portion of the spectrum, the emitted fluorescence typically spans wavelengths from the green to the red (470 nm to 700 nm).
- the emitted autofluorescence light 31 is collected and split into two wavelength bands by the optical splitter 13 .
- An image forming element (e.g. lens assembly) 41 in the optical splitter 13 collects the emitted fluorescence light and forms an image of the tissue at infinity. The image can be focused at infinity via focus mechanism 44 .
- the light is directed onto a dichroic mirror 42 resulting in the autofluorescence light being split into two wavelength bands.
- a portion of the light in one wavelength band passes straight through the dichroic mirror 42 and enters the first optical channel 14 .
- the remaining light in the second wavelength band is reflected by the dichroic mirror 42 .
- the dichroic mirror 42 will pass light having wavelengths less than 570 nm and will reflect light having wavelengths greater than 570 nm.
- the light reflected by the dichroic mirror is again reflected by a mirror 43 into the second optical channel 15 .
- the autofluorescence light that passes straight through the dichroic mirror 42 enters the first optical channel 14 .
- autofluorescence light with wavelengths within a defined band is amplified and formed into an image.
- the optical channel 14 consists of an emission filter 52 , a lens assembly 53 , an image intensifier 54 with phosphor screen 55 and power supply 56 .
- Emission filter 52 passes only the autofluorescence light in a band of wavelengths near the maximum in the tissue spectral emission (typically 490 nm to 560 nm).
- the emission filter 52 should have particularly good blocking characteristics for light in the wavelength band utilized for fluorescence excitation-typically less than 1 in 10 5 of the excitation light passes the emission filter 52 .
- the lens 53 forms an image with the autofluorescence light on the input of the image intensifier 54 .
- the image intensifier is a device that amplifies the light by a gain determined by a bias voltage that is supplied by power supply 56 .
- the image intensifier produces an output image on a phosphor screen 55 (actually an integral part of the image intensifier).
- the power supply 56 is controlled by a controller 71 within the control module 17 .
- the controller 71 controls the output of the power supply 56 in such a way that the intensifier has the appropriate gain for the light input into the system and is protected from overexposure.
- the image intensifier phosphor screen 55 preferably has a long persistence so that the amplified image would be visible for a few seconds.
- the phosphor screen 55 would produce light of a specific wavelength band, for example green light mainly in the band 500 nm to 560 nm.
- the light from the image on the phosphor screen 55 is input to the optical combiner 16 .
- the second optical channel 15 consists of an emission filter 62 , a lens 63 , an image intensifier 64 with phosphor screen 65 and power supply 66 .
- the second optical channel 15 is nearly identical to the first optical channel 14 except that the emission filter 62 is different than emission filter 52 in that filter 62 passes light of a different wavelength band (e.g. passes red light in the band 630 to 750 nm).
- the phosphor screen 65 produces light of a different wavelength (e.g.
- the gain of the image intensifier 64 as set by the controller 71 and power supply 66 may be different than the gain of image intensifier 54 .
- the image formed on phosphor screen 65 is from a different autofluorescence band and may be of different brightness.
- the light from the image on phosphor screen 65 is supplied as an input to the optical combiner 16 .
- the optical combiner 16 consists of a lens 81 , a lens 82 , a dichroic mirror 83 , a mirror 84 , a lens 85 , and a light sensor 86 .
- the lens 81 collects light from the image on phosphor screen 55 , and in combination with lens 85 relays the image from the phosphor screen to the user's eye 19 .
- Light from the image on phosphor screen 55 in one wavelength band (e.g. green light) passes straight through dichroic mirror 83 .
- the dichroic mirror 83 has, for example, characteristics such that light at wavelengths shorter than 570 nm passes straight through and light at wavelengths longer than 570 nm is reflected.
- Lens 82 collects light from the second optical channel in a second wavelength band (e.g. red light) from the image on phosphor screen 65 .
- Lens 82 in combination with lens 85 relays the image from phosphor screen 65 to the user's eye 19 .
- the light from phosphor screen 65 is reflected both by mirror 84 and dichroic mirror 83 . This results, in combination with the image from phosphor screen 55 that passed straight through the dichroic mirror 83 , in the formation of a combined image a the user's eye 19 made up of the images from phosphor screens 55 and 65 .
- the magnifications of lenses 81 and 82 are chosen so that the images from phosphor screens 55 and 65 are the same size at the user's eye, even though the optical path lengths are different.
- dichroic mirror 83 In addition to passing straight through dichroic mirror 83 , a small proportion of the light from phosphor screen 55 is reflected by the dichroic mirror (typically 5%) onto sensor 86 . This light is converted into an electrical signal proportional to the light amplitude, which is measured by the control module 17 .
- the control module 17 consists of the controller 71 , acquire image pushbutton 72 , and brightness adjustment knob 73 .
- the controller 71 contains circuitry to control the light source power supply 21 and image intensifier power supplies 56 , 66 , as well as, circuitry that measures the output voltage of light sensor 86 .
- the acquire image pushbutton 72 is activated by the user to signal to the controller to start the image acquisition sequence when the device is operated in a pulsed mode.
- the brightness adjustment knob 73 is utilized by the user to communicate an adjustable reference point for the brightness of the image to the controller.
- the brightness of the image seen by the user is automatically controlled by the controller 71 based on a combination of measurement of light intensity by the light sensor 86 , the reference brightness from the brightness adjustment knob 73 , and stored image intensifier calibration characteristics.
- the controller 71 utilizes this information to control the light source intensity and duration, as well as the gain of image intensifiers 54 and 64 .
- the control algorithm is designed to operate at the maximum possible light source intensity and pulse duration and minimum intensifier gains. The control algorithm first adjusts the light source intensity and duration (when pulsed) to achieve the desired brightness.
- the algorithm then adjusts the gain of image intensifier 54 to achieve the target brightness and then adjusts the gain of image intensifier 64 in such a way that the ratio of the gain of intensifier 54 to the gain of intensifier 64 is constant, based on the calibration parameters. In this way, the color of the combined image is made to be independent of the brightness of the image and independent of the distance between the tissue and the device.
- the color of the resulting combined image depends on the degree of abnormality of the tissue.
- the spectral characteristics of autofluorescence light emitted by the tissue depend on the degree of abnormality.
- the autofluorescence light emission of abnormal tissue is different in the green portion of the spectrum compared to normal tissue.
- the autofluorescence light emission in the red portion of the spectrum is essentially unchanged when comparing abnormal and normal tissue.
- the brightness of the green component of the combined image varies, depending on the degree of tissue abnormality. Tissue with a degree of abnormality appears a different shade (redder or greener) than normal tissue.
- users can easily discern subtle color differences indicative of abnormal tissue, especially when one area in the field of view is different than the rest.
- a second embodiment of the skin abnormality detection system is also based on FIG. 1 .
- the architecture of the system is the same as the first embodiment and a combined view similar to that shown in FIG. 2 is produced, but a different principle of operation is utilized, necessitating different implementation details.
- an image is produced by overlaying images from two different wavelength bands of autofluorescence light.
- the color of the composite image resulting from the first embodiment depends on the health of the tissue, because the intensity of the autofluorescence light forming one of the images (green) is known to be a strong function of the health of the tissue, whereas the intensity of autofluorescence light forming the second image (red) depends weakly on the health of the tissue.
- a composite image is formed based on one image from the wavelength band of autofluorescence light that is a strong function of the health of the tissue (green), and one image formed from reflected excitation light (blue).
- the color of the combined image depends on the health of the tissue, because the intensity of the autofluorescence light forming one image utilized in the composite varies depending on the health of the tissue, whereas the intensity of the reflected light forming the second image of the composite depends only weakly on the health of the tissue.
- the emission filter 62 for the second optical channel 15 transmits light reflected from the tissue of the same wavelength band as the light emitted by the light source (e.g. 400 nm to 450 nm).
- the image intensifier 64 in the second optical channel 15 of the second embodiment does not need to amplify the light as much and can be of lower quality.
- dichroic mirror 42 is designed to transmit light with shorter wavelengths, for example ⁇ 570 nm in the first embodiment, there is no need to utilize a different dichroic mirror for the second embodiment.
- dichroic mirrors typically reflect 5% of the incident light in region they transmit, so the dichroic mirror 42 specified in the first embodiment can be utilized to reduce the intensity of the light reflected from the tissue going into the second optical channel 15 .
- a dichroic mirror that transmits in the green and reflects in the blue e.g. reflects wavelengths ⁇ 470 nm and transmits wavelengths >470 nm
- a neutral density filter or low gain image intensifier can be utilized.
- a third embodiment of the skin abnormality detection system is also based on the architecture of FIG. 1 and produces a combined view similar to that shown in FIG. 2 .
- the third embodiment utilizes the same principle of operation as the second embodiment, but differs in the implementation details.
- a combined image is formed from the combination of a fluorescence image and a reflected image. The difference is that instead of utilizing the excitation light as the source of light for the reflected image, the light source 10 outputs light expressly for the purpose of producing a reflected image, at a wavelength that is longer than that utilized for the detection of fluorescence.
- the excitation filter 26 in the third embodiment has two passbands, one passing short wavelengths for fluorescence excitation (for example 400 nm to 450 nm), and one passing longer wavelengths for the reflected image (for example 630 nm to 700 nm).
- the filter preferably has very good blocking characteristics in the wavelength region where fluorescence is detected (e.g. less than 10 ⁇ 5 of the incident light should be transmitted between 470 nm and 600 nm).
- the emission filter 62 passes light in the longer wavelength band which is used for the reflected image (for example 630 nm to 700 nm).
- This filter 62 should have good blocking of the light in the excitation wavelength band (400 nm to 450 nm in this example).
- the emission filter 52 must, in addition to the characteristics described for the first embodiment, also have good blocking of light in the band used for the reflect image (for example, in the band 630 nm to 700 nm less than 10 5 of the light should pass the filter).
- the balance of the system is similar to that of the second embodiment.
- FIG. 3 A fourth embodiment of the skin abnormality detection system according to the present invention is shown in FIG. 3 .
- the fourth embodiment is a viewer that produces a combined, binocular image based on images either from two wavelength bands of emitted autofluorescence light, or from one wavelength band of emitted autofluorescence light and one wavelength band of reflected light.
- the system described in the fourth embodiment can be obtained by combining two of the systems (ie., one for each eye) described in one of the first three embodiments to obtain a binocular view.
- the imaging system 100 includes a power source 102 , a control module 104 and a fight source 106 that supplies light to excite a tissue sample 108 to produce autofluorescence light.
- a left imaging system 5 L provides a superimposed autofluorescence image to a viewer's left eye in the same manner as the system shown in FIG. 1 and described above.
- An imaging system 5 R provides a superimposed autofluorescence image for a viewer's right eye in the same manner as the system 5 shown in FIG. 1 .
- FIG. 4 A fifth embodiment of the skin abnormality detection system is shown in FIG. 4 .
- the fifth embodiment is an optical system that produces a combined image based on images from two wavelength bands of emitted autofluorescence light.
- the fifth embodiment is similar to the first embodiment, except that it is intended to be utilized with an instant camera or a digital camera instead of the user's eye.
- a combined view, similar to that shown in FIG. 2 is recorded and displayed by means of the camera.
- the fifth embodiment of a skin abnormality detection system is made up of eight major subsystems: a light source 10 that produces excitation light that will cause the tissue 12 under examination to produce characteristic autofluorescence light, an optical splitter 13 that divides the fluorescence light received from the tissue into two beams, a first optical channel 14 that collects, amplifies, and images the light in one fluorescence wavelength band, a second optical channel 15 that collects, amplifies, and images the light in a second fluorescence wavelength band, an optical combiner 16 that combines the images from the two fluorescence optical channels into one and presents the combined image to a digital or instant camera 120 which records the image for viewing, a control module 17 , and a power source 18 .
- a light source 10 that produces excitation light that will cause the tissue 12 under examination to produce characteristic autofluorescence light
- an optical splitter 13 that divides the fluorescence light received from the tissue into two beams
- a first optical channel 14 that collects, amplifies, and images the light in one fluor
- the power source 18 could be batteries or the AC line. In the preferred embodiment, battery power is utilized for portability.
- the light source 10 provides light of the required characteristics for exciting the tissue fluorescence. It consists of a power supply 21 which is controlled by the control module 17 and which receives electrical power from power source 18 .
- the power supply outputs electrical power of the appropriate characteristics to operate lamp 22 .
- the lamp which may be a xenon flash lamp, produces a broad spectrum output of visible light (e.g. white light).
- the light is formed into a beam onto the tissue 12 by reflector 23 and the combination of image forming elements 24 and 25 (e.g. lenses). In addition to forming a beam, a region of collimated light is produced between the two lenses that provides optimal conditions for the placement of an optical band pass filter, excitation filter 26 .
- This filter 26 is designed for incident light to be perpendicular to the filter surface.
- the excitation filter 16 characteristics are such that the filter passes light of wavelengths utilized to excite fluorescence (typically 400 nm to 450 nm) and blocks light of other wavelengths. It is important that the filter block light in the wavelength bands where fluorescence is detected (i.e. in those bands no more than 1 in 10 5 of the light from the lamp can pass the filter).
- the lamp 22 is operated in a pulsed mode similar to a camera flash.
- the advantages of operating in the pulsed mode are that it allows the system to be utilized in an undarkened room and the power required is reduced so battery operation is possible.
- the intensity and duration of the light (when pulsed) are controlled by the control module 17 as a means of adjusting the brightness of the image as detected by the camera 120 .
- the result of illuminating the tissue 12 with excitation light is the emission of characteristic autofluorescence light 31 by the tissue. If the excitation light is in the blue, the emitted fluorescence typically spans wavelengths from the green to the red (470 nm to 700 nm).
- the emitted autofluorescence light 31 is collected and split into two wavelength bands by the optical splitter 13 .
- An image forming element (e.g. lens) 41 in the optical splitter collects the emitted fluorescence light and forms an image of the tissue.
- the position of the lens 41 can be moved via focus mechanism 44 to focus the image.
- the light is directed onto a dichroic mirror 42 resulting in the autofluorescence light being split into two wavelength bands.
- a portion of the light in one wavelength band passes straight through the dichroic mirror and enters the first optical channel 14 .
- the remaining light in the second wavelength band is reflected by the dichroic mirror 42 .
- the dichroic mirror 42 will pass light having wavelengths less than 570 nm and will reflect light having wavelengths greater than 570 nm.
- the light reflected by the dichroic mirror is again reflected by a mirror 43 into the second optical channel 15 .
- the autofluorescence light that passes straight through the dichroic mirror 42 enters the first optical channel 14 .
- autofluorescence light with wavelengths within a defined band is amplified and formed into an image.
- the optical channel 14 consists of a lens 53 , an emission filter 52 , an image intensifier 54 with phosphor screen 55 and power supply 56 .
- the lens 53 forms an image at an infinite distance to collimate the light. This results in an optimum location for the emission filter 52 that is designed to filter incident light perpendicular to the filter's surface.
- Emission filter 52 passes only the autofluorescence light in a band of wavelengths near the maximum in the tissue spectral emission (typically 490 nm to 560 nm).
- the emission filter preferably has good blocking characteristics for light in the wavelength band utilized for fluorescence excitation. Typically less than 1 in 10 5 of the excitation light passes the emission filter.
- the lens 53 forms an image with the autofluorescence light on the input of the image intensifier 54 .
- the image intensifier amplifies the incoming light by a gain determined by a bias voltage supplied by power supply 56 .
- the image intensifier produces an output image on phosphor screen 55 .
- the power supply 56 is controlled by the control module 17 .
- the control module controls the output of the power supply in such a way that the intensifier has the appropriate gain for the light input to the system.
- the image intensifier phosphor screen 55 has a persistence of at least a few milliseconds, and produces light of a specific wavelength, for example green light mainly in the band 500 nm to 560 nm.
- the light from the image on the phosphor screen is input to the optical combiner 16 .
- the second optical channel 15 consists of a lens 63 , an emission filter 62 , an image intensifier 64 with phosphor screen 65 and power supply 66 .
- the second optical channel 15 is nearly identical to the first optical channel 14 except that the emission filter 62 is different than emission filter 52 in that filter 62 passes light of a different wavelength band (e.g. red light in the band 630 to 750 nm), phosphor screen 65 produces light of different wavelength (e.g.
- the gain of the image intensifier 64 as set by controller 71 and power supply 66 may be different than the gain of image intensifier 54 .
- the image formed on phosphor screen 65 is from a different autofluorescence band and may be of different brightness.
- the light from the image on phosphor screen 65 is input to the optical combiner 16 .
- the optical combiner 16 consists of lens 81 , lens 82 , dichroic mirror 83 , mirror 84 and lens 85 .
- Lens 81 collects light from the image on phosphor screen 55 , and in combination with lens 85 relays the image from the phosphor screen to the camera's 120 optical system.
- Light from the image on phosphor screen 55 in one wavelength band (e.g. green light) passes straight through dichroic mirror 83 .
- the dichroic mirror 83 has, for example, characteristics such that light at wavelengths shorter than 570 nm passes straight through and light at wavelengths longer than 570 nm is reflected.
- Lens 82 collects light from the second optical channel in a second wavelength band (e.g. red light) from the image on phosphor screen 55 .
- a second wavelength band e.g. red light
- Lens 82 in combination with lens 85 relays the image from phosphor screen 65 to the camera's 120 optical system.
- the light from phosphor. screen 65 is reflected both by mirror 84 and dichroic mirror 83 .
- the magnifications of lenses 81 and 82 are chosen so that the images from phosphor screens 55 and 65 are the same size at the camera's optical system, even though the optical path lengths are different.
- the fifth embodiment of a skin abnormality detection system attaches to a digital or instant camera 120 by means of the camera lens mount 122 , or by means of a screw in filter mount on the camera's lens.
- the control module 17 consists of a controller 71 , and brightness adjustment knob 72 .
- the controller 71 contains circuitry to control the light source power supply and image intensifier power supplies.
- the shutter button 123 on the camera is activated by the user to start the image acquisition sequence.
- the camera sends a signal to the controller 71 through the flash synchronization output jack 121 indicating that image acquisition is to start and related to the image brightness.
- the controller makes use of this signal in controlling the light source power supply and image intensifier power supplies as described below.
- the brightness adjustment knob 72 is utilized by the user to communicate an adjustable reference point for the brightness of the image to the controller.
- the brightness of the image as seen by the user is automatically controlled by the controller 71 based on a combination of measurement of light intensity by the camera light meter, the reference brightness from the brightness adjustment knob 72 , and stored image intensifier calibration characteristics.
- the controller 71 utilizes this information to control the light source intensity and duration, as well as the gain of image intensifiers 54 and 64 .
- the image intensifiers, -controlled through their power supplies, are turned on by the controller 71 only during the period that the light source outputs light, plus an additional period while the fluorescence decays (typically 100 microseconds).
- the camera's shutter is opened for a time much longer than the duration of the light source output (typically ⁇ fraction (1/125) ⁇ of a second).
- control algorithm In order to achieve the best image quality, the control algorithm is designed to operate at the maximum possible light source intensity and pulse duration and minimum intensifier gains.
- the control algorithm first adjusts the light source intensity and duration to achieve the desired brightness as indicated by the camera light meter. Following this the algorithm adjusts the gain of image intensifier 54 as further required to achieve the desired brightness and then adjusts the gain of image intensifier 64 in such a way that the ratio of the gain of intensifier 54 to the gain of intensifier 64 is constant, based on the calibration parameters. In this way, the color of the combined image is made to be independent of the brightness of the image and independent of the distance between the tissue and the device.
- a sixth embodiment of the skin abnormality detection system is also based on the embodiment shown in FIG. 4 .
- the architecture of the system is the same as the fifth embodiment and a combined view similar to that shown in FIG. 2 is produced, but a different principle of operation is utilized, necessitating different implementation details.
- the sixth embodiment is similar to the second embodiment except that the sixth embodiment utilizes a camera to store the image whereas the second embodiment is a viewer.
- an image is produced by overlaying images from two different wavelength bands of autofluorescence light.
- the color of the composite image resulting from the first embodiment depends on the health of the tissue, because the intensity of the autofluorescence light forming one of the images (green) is known to be a strong function of the health of the tissue, whereas the intensity of autofluorescence light forming the second image (red) depends weakly on the health of the tissue.
- a composite image is formed based on one image from the wavelength band of autofluorescence light that is a strong function of the health of the tissue (green), and one image formed from reflected excitation light (blue).
- the color of the combined image depends on the health of the tissue, because the intensity of the autofluorescence light forming one image utilized in the composite varies depending on the health of the tissue, whereas the intensity of the reflected light forming the second image of the composite depends only weakly on the health of the tissue.
- the emission filter 62 for the second optical channel transmits light reflected from the tissue of the same wavelength band as the light emitted by the light source (e.g. 400 nm to 450 nm).
- the image intensifier 64 in the second optical channel 15 of the second embodiment does not need to amplify the light as much and can be of lower quality.
- dichroic mirror 42 is designed to transmit light with shorter wavelengths, for example ⁇ 570 nm in the first embodiment, there is no need to utilize a different dichroic mirror in this embodiment.
- dichroic mirrors reflect 5% of the incident light in region they transmit, so the dichroic mirror as specified in the fifth embodiment can be utilized to reduce the intensity of the light reflected from the tissue going into the second optical channel 15 .
- a dichroic mirror that transmits in the green and reflects in the blue e.g. reflects wavelengths ⁇ 470 nm and transmits wavelengths >470 nm
- a neutral density filter or low gain image intensifier can be utilized.
- a seventh embodiment of the skin abnormality detection system is also based on the architecture of FIG. 4 and produces a combined view similar to that shown in FIG. 2 .
- the seventh embodiment utilizes the same principle of operation as the sixth embodiment, but differs in the implementation details.
- the seventh embodiment is similar to the third embodiment except that the seventh embodiment utilizes a camera to store the image whereas the third embodiment is a viewer.
- a combined image. is formed from the combination of a fluorescence image and a reflected image. The difference is that instead of utilizing the excitation light as the source of light for the reflected image, the light source 10 outputs light expressly for the purpose of producing a reflected image, at a wavelength longer than that utilized for the detection of fluorescence.
- the excitation filter 26 in the seventh embodiment light source has two passbands, one passing short wavelengths for fluorescence excitation (for example 400 nm to 450 nm),. and one passing longer wavelengths for the reflected image (for example 630 nm to 700 mn).
- the filter preferably has very good blocking characteristics in the wavelength region where fluorescence is detected (e.g. less than 10 ⁇ 5 of the incident light should be transmitted between 470 nm and 600 nm).
- the emission filter 62 must also pass light in the longer wavelength band which is used for the reflected image (for example 630 nm to 700 nm).
- This filter should have good blocking of the light in the excitation wavelength band (400 nm to 450 nm in this example).
- the emission filter 52 must, in addition to the characteristics described for the fifth embodiment, also have good blocking of light in the band used for the reflect image (for example, in the band 630 nm to 700 nm less than 10 ⁇ 5 of the light should pass the filter).
- the balance of the system is similar to that of the sixth embodiment.
- the present invention is not limited to the detection of skin cancer but can be used to detect other types of lesions that exhibit variations in autofluorescence intensities.
- the invention may also be utilized in internal organs such as the mouth or during surgical procedures.
- the abnormality detection may also be coupled to a scope, such as an endoscope or laproscope, used in the medical field to examine internal tissues and organs.
- the embodiments described may also be used with tissue where photodynamic agents, which enhance the fluorescence response, have been introduced.
- the detection system may be used not only on skin, but also on other surfaces, such as the detection of abnormalities on plants, and the detection of contaminants on non-living surfaces, such as surgical tools or food. It is, therefore, intended that the scope of the invention be determined from the following claims and equivalents thereto.
Abstract
Description
Claims (33)
Priority Applications (8)
Application Number | Priority Date | Filing Date | Title |
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US09/469,562 US6603552B1 (en) | 1999-12-22 | 1999-12-22 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
PCT/US2000/034052 WO2001045557A1 (en) | 1999-12-22 | 2000-12-14 | Portable system for detecting skin abnormalities |
EP00986421A EP1239771B1 (en) | 1999-12-22 | 2000-12-14 | Portable system for detecting skin abnormalities |
DE60014702T DE60014702T2 (en) | 1999-12-22 | 2000-12-14 | PORTABLE SYSTEM FOR THE DETERMINATION OF SKIN ANOMALIES |
JP2001546299A JP4727886B2 (en) | 1999-12-22 | 2000-12-14 | Portable system for detecting skin abnormalities |
AU22661/01A AU2266101A (en) | 1999-12-22 | 2000-12-14 | Portable system for detecting skin abnormalities |
US10/438,551 US20030206301A1 (en) | 1999-12-22 | 2003-05-14 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
US10/830,680 US20040196463A1 (en) | 1999-12-22 | 2004-04-22 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
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US09/469,562 US6603552B1 (en) | 1999-12-22 | 1999-12-22 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
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US10/830,680 Abandoned US20040196463A1 (en) | 1999-12-22 | 2004-04-22 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
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US10/830,680 Abandoned US20040196463A1 (en) | 1999-12-22 | 2004-04-22 | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
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Cited By (81)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20020035330A1 (en) * | 2000-07-14 | 2002-03-21 | Xillix Technologies Corporation | Compact fluorescent endoscopy video system |
US20030045799A1 (en) * | 2001-07-09 | 2003-03-06 | L'oreal | Device, system and method for observing a typological characteristic of the body |
US20030158470A1 (en) * | 2000-09-18 | 2003-08-21 | Sti Medical Systems, Inc. | Dual mode real-time screening and rapid full-area, selective-spectral, remote imaging and analysis device and process |
US20030206301A1 (en) * | 1999-12-22 | 2003-11-06 | Xillix Technologies Corporation | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
US20040212609A1 (en) * | 2003-04-24 | 2004-10-28 | Yoichi Igarashi | Inspecting method and inspecting device of control signal for display device, and display unit having this inspecting function |
US20050094099A1 (en) * | 2003-10-30 | 2005-05-05 | Welch Allyn, Inc. | Apparatus and method for diagnosis of optically identifiable ophthalmic conditions |
US6899675B2 (en) | 2002-01-15 | 2005-05-31 | Xillix Technologies Corp. | Fluorescence endoscopy video systems with no moving parts in the camera |
US20060025658A1 (en) * | 2003-10-30 | 2006-02-02 | Welch Allyn, Inc. | Apparatus and method of diagnosis of optically identifiable ophthalmic conditions |
US20060092315A1 (en) * | 2004-10-29 | 2006-05-04 | Johnson & Johnson Consumer Companies, Inc. | Skin Imaging system with probe |
US20060126127A1 (en) * | 2004-12-09 | 2006-06-15 | Stanback John H | System and method for detecting and correcting defective pixels in a digital image sensor |
US20060210132A1 (en) * | 2005-01-19 | 2006-09-21 | Dermaspect, Llc | Devices and methods for identifying and monitoring changes of a suspect area on a patient |
US20060241496A1 (en) * | 2002-01-15 | 2006-10-26 | Xillix Technologies Corp. | Filter for use with imaging endoscopes |
US20060264761A1 (en) * | 2005-03-18 | 2006-11-23 | Jochem Knoche | Portable fluorescence scanner for molecular signatures |
US20070002479A1 (en) * | 2005-06-29 | 2007-01-04 | Johnson & Johnson Consumer Companies, Inc. | Apparatus and method for viewing the skin |
US20070004972A1 (en) * | 2005-06-29 | 2007-01-04 | Johnson & Johnson Consumer Companies, Inc. | Handheld device for determining skin age, proliferation status and photodamage level |
US20080080755A1 (en) * | 2006-10-02 | 2008-04-03 | Gregory Payonk | Apparatus and Method for Measuring Photodamage to Skin |
US20080079843A1 (en) * | 2006-10-02 | 2008-04-03 | Jeffrey Pote | Imaging Apparatus and Methods for Capturing and Analyzing Digital Images of the Skin |
US20080177140A1 (en) * | 2007-01-23 | 2008-07-24 | Xillix Technologies Corp. | Cameras for fluorescence and reflectance imaging |
US20090124854A1 (en) * | 2007-11-09 | 2009-05-14 | Fujifilm Corporation | Image capturing device and image capturing system |
US20090270717A1 (en) * | 2008-04-25 | 2009-10-29 | Welch Allyn, Inc. | Apparatus and method for diagnosis of optically identifiable ophthalmic conditions |
US20100016711A1 (en) * | 2008-07-21 | 2010-01-21 | University Of South Carolina | Membrane-Deformation Mapping Technique |
WO2010011763A1 (en) * | 2008-07-22 | 2010-01-28 | Jaafar Tindi | Handheld apparatus to determine the viability of a biological tissue |
US7713265B2 (en) | 2006-12-22 | 2010-05-11 | Ethicon Endo-Surgery, Inc. | Apparatus and method for medically treating a tattoo |
US7738032B2 (en) | 2001-11-08 | 2010-06-15 | Johnson & Johnson Consumer Companies, Inc. | Apparatus for and method of taking and viewing images of the skin |
US20100249545A1 (en) * | 2009-03-24 | 2010-09-30 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US20110054310A1 (en) * | 2009-08-31 | 2011-03-03 | John David Taylor | Portable medical imaging apparatus for documentation of dermatological areas and subjects of interest |
US7925333B2 (en) | 2007-08-28 | 2011-04-12 | Ethicon Endo-Surgery, Inc. | Medical device including scanned beam unit with operational control features |
US20110164249A1 (en) * | 2009-11-04 | 2011-07-07 | Olympus Corporation | Light spectrum detection method |
US7982776B2 (en) | 2007-07-13 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | SBI motion artifact removal apparatus and method |
US7983739B2 (en) | 2007-08-27 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | Position tracking and control for a scanning assembly |
US7995045B2 (en) | 2007-04-13 | 2011-08-09 | Ethicon Endo-Surgery, Inc. | Combined SBI and conventional image processor |
US8050520B2 (en) | 2008-03-27 | 2011-11-01 | Ethicon Endo-Surgery, Inc. | Method for creating a pixel image from sampled data of a scanned beam imager |
US8160678B2 (en) | 2007-06-18 | 2012-04-17 | Ethicon Endo-Surgery, Inc. | Methods and devices for repairing damaged or diseased tissue using a scanning beam assembly |
US8216214B2 (en) | 2007-03-12 | 2012-07-10 | Ethicon Endo-Surgery, Inc. | Power modulation of a scanning beam for imaging, therapy, and/or diagnosis |
US8273015B2 (en) | 2007-01-09 | 2012-09-25 | Ethicon Endo-Surgery, Inc. | Methods for imaging the anatomy with an anatomically secured scanner assembly |
AU2011242140B2 (en) * | 2004-04-14 | 2012-11-29 | Led Medical Diagnostics, Inc. | Systems and methods for detection of disease including oral scopes and ambient light management systems (ALMS) |
US8332014B2 (en) | 2008-04-25 | 2012-12-11 | Ethicon Endo-Surgery, Inc. | Scanned beam device and method using same which measures the reflectance of patient tissue |
EP2554107A1 (en) * | 2011-08-05 | 2013-02-06 | GC Corporation | Intraoral inspection apparatus and method for operating intraoral inspection apparatus |
WO2013117330A1 (en) * | 2012-02-06 | 2013-08-15 | Carl Zeiss Meditec Ag | Method and device for examining a biological tissue by analysing fluorescence response to illumination and for treating the tissue |
US8532736B1 (en) * | 2005-07-29 | 2013-09-10 | Hewlett-Packard Development Company, L.P. | Apparatus and a method for quantifying properties of skin |
US8626271B2 (en) | 2007-04-13 | 2014-01-07 | Ethicon Endo-Surgery, Inc. | System and method using fluorescence to examine within a patient's anatomy |
US8715173B2 (en) * | 2012-03-12 | 2014-05-06 | United Sciences, Llc | Otoscanner with fan and ring laser |
US8801606B2 (en) | 2007-01-09 | 2014-08-12 | Ethicon Endo-Surgery, Inc. | Method of in vivo monitoring using an imaging system including scanned beam imaging unit |
US8825140B2 (en) | 2001-05-17 | 2014-09-02 | Xenogen Corporation | Imaging system |
US8900126B2 (en) | 2011-03-23 | 2014-12-02 | United Sciences, Llc | Optical scanning device |
US9042967B2 (en) | 2008-05-20 | 2015-05-26 | University Health Network | Device and method for wound imaging and monitoring |
EP2888989A1 (en) | 2013-12-31 | 2015-07-01 | Karl Storz Imaging, Inc. | Switching between white light imaging and excitation light imaging leaving last video frame displayed |
US9079762B2 (en) | 2006-09-22 | 2015-07-14 | Ethicon Endo-Surgery, Inc. | Micro-electromechanical device |
US9125552B2 (en) | 2007-07-31 | 2015-09-08 | Ethicon Endo-Surgery, Inc. | Optical scanning module and means for attaching the module to medical instruments for introducing the module into the anatomy |
US20160058362A1 (en) * | 2013-04-18 | 2016-03-03 | Koninklijke Philips N.V. | Acquiring cervical images |
US9386909B2 (en) | 2006-07-28 | 2016-07-12 | Novadaq Technologies Inc. | System and method for deposition and removal of an optical element on an endoscope objective |
US9610021B2 (en) | 2008-01-25 | 2017-04-04 | Novadaq Technologies Inc. | Method for evaluating blush in myocardial tissue |
US9642532B2 (en) | 2008-03-18 | 2017-05-09 | Novadaq Technologies Inc. | Imaging system for combined full-color reflectance and near-infrared imaging |
US9816930B2 (en) | 2014-09-29 | 2017-11-14 | Novadaq Technologies Inc. | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US9814378B2 (en) | 2011-03-08 | 2017-11-14 | Novadaq Technologies Inc. | Full spectrum LED illuminator having a mechanical enclosure and heatsink |
US9877654B2 (en) | 2006-02-07 | 2018-01-30 | Novadaq Technologies Inc. | Near infrared imaging |
US9955910B2 (en) | 2005-10-14 | 2018-05-01 | Aranz Healthcare Limited | Method of monitoring a surface feature and apparatus therefor |
US20180180477A1 (en) * | 2015-09-01 | 2018-06-28 | Carl Zeiss Meditec Ag | Optical filter system and fluorescence detection system |
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Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
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Citations (42)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4200801A (en) | 1979-03-28 | 1980-04-29 | The United States Of America As Represented By The United States Department Of Energy | Portable spotter for fluorescent contaminants on surfaces |
US4532918A (en) | 1983-10-07 | 1985-08-06 | Welch Allyn Inc. | Endoscope signal level control |
US4556057A (en) | 1982-08-31 | 1985-12-03 | Hamamatsu Tv Co., Ltd. | Cancer diagnosis device utilizing laser beam pulses |
US4786813A (en) | 1984-10-22 | 1988-11-22 | Hightech Network Sci Ab | Fluorescence imaging system |
US4821117A (en) | 1986-11-12 | 1989-04-11 | Kabushiki Kaisha Toshiba | Endoscopic system for producing fluorescent and visible images |
US4930516A (en) | 1985-11-13 | 1990-06-05 | Alfano Robert R | Method for detecting cancerous tissue using visible native luminescence |
US5134662A (en) | 1985-11-04 | 1992-07-28 | Cell Analysis Systems, Inc. | Dual color camera microscope and methodology for cell staining and analysis |
EP0512965A1 (en) | 1991-05-08 | 1992-11-11 | Xillix Technologies Corporation | Endoscopic imaging system for diseased tissue |
US5165079A (en) | 1989-02-02 | 1992-11-17 | Linotype-Hell Ag | Optical color-splitter arrangement |
US5214503A (en) | 1992-01-31 | 1993-05-25 | The United States Of America As Represented By The Secretary Of The Army | Color night vision camera system |
US5225883A (en) | 1991-06-05 | 1993-07-06 | The Babcock & Wilcox Company | Video temperature monitor |
US5255087A (en) | 1986-11-29 | 1993-10-19 | Olympus Optical Co., Ltd. | Imaging apparatus and endoscope apparatus using the same |
US5365057A (en) | 1993-07-02 | 1994-11-15 | Litton Systems, Inc. | Light-weight night vision device |
US5371355A (en) | 1993-07-30 | 1994-12-06 | Litton Systems, Inc. | Night vision device with separable modular image intensifier assembly |
US5377686A (en) | 1991-10-11 | 1995-01-03 | The University Of Connecticut | Apparatus for detecting leakage from vascular tissue |
US5419323A (en) | 1988-12-21 | 1995-05-30 | Massachusetts Institute Of Technology | Method for laser induced fluorescence of tissue |
US5420628A (en) | 1990-01-16 | 1995-05-30 | Research Development Foundation | Video densitometer with determination of color composition |
US5421337A (en) | 1989-04-14 | 1995-06-06 | Massachusetts Institute Of Technology | Spectral diagnosis of diseased tissue |
US5424841A (en) | 1993-05-28 | 1995-06-13 | Molecular Dynamics | Apparatus for measuring spatial distribution of fluorescence on a substrate |
JPH07155285A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing endoscope apparatus |
JPH07155292A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing apparatus |
JPH07155286A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing apparatus |
JPH07155290A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Endoscope apparatus |
JPH07155291A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observation apparatus |
US5430476A (en) | 1992-06-24 | 1995-07-04 | Richard Wolf Gmbh | Device for supplying light to endoscopes |
JPH07204156A (en) | 1993-12-03 | 1995-08-08 | Olympus Optical Co Ltd | Fluorescence observation device |
JPH07250812A (en) | 1994-03-15 | 1995-10-03 | Olympus Optical Co Ltd | Fluorescence diagnosing apparatus |
JPH07250804A (en) | 1994-03-15 | 1995-10-03 | Olympus Optical Co Ltd | Fluorescence observer |
WO1995026673A2 (en) | 1994-03-28 | 1995-10-12 | Xillix Technologies Corporation | Apparatus and method for imaging diseased tissue using integrated autofluorescence |
JPH08224208A (en) | 1995-02-22 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescence observing endoscope device |
JPH08224240A (en) | 1995-02-22 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescent diagnosing device |
JPH08224209A (en) | 1995-02-23 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescence observing device |
DE19608027A1 (en) | 1995-03-03 | 1996-09-05 | Asahi Optical Co Ltd | Biological fluorescence diagnosis device for medical use |
US5647368A (en) | 1996-02-28 | 1997-07-15 | Xillix Technologies Corp. | Imaging system for detecting diseased tissue using native fluorsecence in the gastrointestinal and respiratory tract |
JPH10104070A (en) | 1996-09-30 | 1998-04-24 | Oyo Koden Kenkiyuushitsu:Kk | Frequency standard and method for forming selected standard frequency |
JPH10151104A (en) | 1996-11-25 | 1998-06-09 | Olympus Optical Co Ltd | Fluorescent endoscope device |
WO1998024360A1 (en) | 1996-12-04 | 1998-06-11 | Harvey Lui | Fluorescence scope system for dermatologic diagnosis |
JPH10201700A (en) | 1997-01-20 | 1998-08-04 | Olympus Optical Co Ltd | Fluoroscopic endoscope device |
JPH11155812A (en) | 1997-12-02 | 1999-06-15 | Olympus Optical Co Ltd | Fluorescent observation device |
US6008889A (en) | 1997-04-16 | 1999-12-28 | Zeng; Haishan | Spectrometer system for diagnosis of skin disease |
WO2000042910A1 (en) | 1999-01-26 | 2000-07-27 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
US6148227A (en) | 1998-01-07 | 2000-11-14 | Richard Wolf Gmbh | Diagnosis apparatus for the picture providing recording of fluorescing biological tissue regions |
Family Cites Families (1)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6603552B1 (en) * | 1999-12-22 | 2003-08-05 | Xillix Technologies Corp. | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
-
1999
- 1999-12-22 US US09/469,562 patent/US6603552B1/en not_active Expired - Lifetime
-
2003
- 2003-05-14 US US10/438,551 patent/US20030206301A1/en not_active Abandoned
-
2004
- 2004-04-22 US US10/830,680 patent/US20040196463A1/en not_active Abandoned
Patent Citations (49)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4200801A (en) | 1979-03-28 | 1980-04-29 | The United States Of America As Represented By The United States Department Of Energy | Portable spotter for fluorescent contaminants on surfaces |
US4556057A (en) | 1982-08-31 | 1985-12-03 | Hamamatsu Tv Co., Ltd. | Cancer diagnosis device utilizing laser beam pulses |
US4532918A (en) | 1983-10-07 | 1985-08-06 | Welch Allyn Inc. | Endoscope signal level control |
US4786813A (en) | 1984-10-22 | 1988-11-22 | Hightech Network Sci Ab | Fluorescence imaging system |
US5134662A (en) | 1985-11-04 | 1992-07-28 | Cell Analysis Systems, Inc. | Dual color camera microscope and methodology for cell staining and analysis |
US4930516A (en) | 1985-11-13 | 1990-06-05 | Alfano Robert R | Method for detecting cancerous tissue using visible native luminescence |
US4930516B1 (en) | 1985-11-13 | 1998-08-04 | Laser Diagnostic Instr Inc | Method for detecting cancerous tissue using visible native luminescence |
US4821117A (en) | 1986-11-12 | 1989-04-11 | Kabushiki Kaisha Toshiba | Endoscopic system for producing fluorescent and visible images |
US5255087A (en) | 1986-11-29 | 1993-10-19 | Olympus Optical Co., Ltd. | Imaging apparatus and endoscope apparatus using the same |
US5419323A (en) | 1988-12-21 | 1995-05-30 | Massachusetts Institute Of Technology | Method for laser induced fluorescence of tissue |
US5165079A (en) | 1989-02-02 | 1992-11-17 | Linotype-Hell Ag | Optical color-splitter arrangement |
US5421337A (en) | 1989-04-14 | 1995-06-06 | Massachusetts Institute Of Technology | Spectral diagnosis of diseased tissue |
US5420628A (en) | 1990-01-16 | 1995-05-30 | Research Development Foundation | Video densitometer with determination of color composition |
EP0512965A1 (en) | 1991-05-08 | 1992-11-11 | Xillix Technologies Corporation | Endoscopic imaging system for diseased tissue |
US5507287A (en) | 1991-05-08 | 1996-04-16 | Xillix Technologies Corporation | Endoscopic imaging system for diseased tissue |
US5225883A (en) | 1991-06-05 | 1993-07-06 | The Babcock & Wilcox Company | Video temperature monitor |
US5377686A (en) | 1991-10-11 | 1995-01-03 | The University Of Connecticut | Apparatus for detecting leakage from vascular tissue |
US5214503A (en) | 1992-01-31 | 1993-05-25 | The United States Of America As Represented By The Secretary Of The Army | Color night vision camera system |
US5430476A (en) | 1992-06-24 | 1995-07-04 | Richard Wolf Gmbh | Device for supplying light to endoscopes |
US5424841A (en) | 1993-05-28 | 1995-06-13 | Molecular Dynamics | Apparatus for measuring spatial distribution of fluorescence on a substrate |
US5365057A (en) | 1993-07-02 | 1994-11-15 | Litton Systems, Inc. | Light-weight night vision device |
US5371355A (en) | 1993-07-30 | 1994-12-06 | Litton Systems, Inc. | Night vision device with separable modular image intensifier assembly |
JPH07155290A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Endoscope apparatus |
JPH07155291A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observation apparatus |
JPH07155292A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing apparatus |
JPH07204156A (en) | 1993-12-03 | 1995-08-08 | Olympus Optical Co Ltd | Fluorescence observation device |
JPH07155286A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing apparatus |
JPH07155285A (en) | 1993-12-03 | 1995-06-20 | Olympus Optical Co Ltd | Fluorescence observing endoscope apparatus |
JPH07250812A (en) | 1994-03-15 | 1995-10-03 | Olympus Optical Co Ltd | Fluorescence diagnosing apparatus |
JPH07250804A (en) | 1994-03-15 | 1995-10-03 | Olympus Optical Co Ltd | Fluorescence observer |
US5827190A (en) | 1994-03-28 | 1998-10-27 | Xillix Technologies Corp. | Endoscope having an integrated CCD sensor |
WO1995026673A2 (en) | 1994-03-28 | 1995-10-12 | Xillix Technologies Corporation | Apparatus and method for imaging diseased tissue using integrated autofluorescence |
US5590660A (en) | 1994-03-28 | 1997-01-07 | Xillix Technologies Corp. | Apparatus and method for imaging diseased tissue using integrated autofluorescence |
JPH08224240A (en) | 1995-02-22 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescent diagnosing device |
JPH08224208A (en) | 1995-02-22 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescence observing endoscope device |
JPH08224209A (en) | 1995-02-23 | 1996-09-03 | Olympus Optical Co Ltd | Fluorescence observing device |
DE19608027A1 (en) | 1995-03-03 | 1996-09-05 | Asahi Optical Co Ltd | Biological fluorescence diagnosis device for medical use |
US5647368A (en) | 1996-02-28 | 1997-07-15 | Xillix Technologies Corp. | Imaging system for detecting diseased tissue using native fluorsecence in the gastrointestinal and respiratory tract |
EP0792618A1 (en) | 1996-02-28 | 1997-09-03 | Xillix Technologies Corporation | Imaging system for detecting diseased tissue using native fluorescence in the gastrointestinal and respiratory tract |
JPH10104070A (en) | 1996-09-30 | 1998-04-24 | Oyo Koden Kenkiyuushitsu:Kk | Frequency standard and method for forming selected standard frequency |
JPH10151104A (en) | 1996-11-25 | 1998-06-09 | Olympus Optical Co Ltd | Fluorescent endoscope device |
WO1998024360A1 (en) | 1996-12-04 | 1998-06-11 | Harvey Lui | Fluorescence scope system for dermatologic diagnosis |
US6021344A (en) | 1996-12-04 | 2000-02-01 | Derma Technologies, Inc. | Fluorescence scope system for dermatologic diagnosis |
JPH10201700A (en) | 1997-01-20 | 1998-08-04 | Olympus Optical Co Ltd | Fluoroscopic endoscope device |
US6008889A (en) | 1997-04-16 | 1999-12-28 | Zeng; Haishan | Spectrometer system for diagnosis of skin disease |
US6069689A (en) | 1997-04-16 | 2000-05-30 | Derma Technologies, Inc. | Apparatus and methods relating to optical systems for diagnosis of skin diseases |
JPH11155812A (en) | 1997-12-02 | 1999-06-15 | Olympus Optical Co Ltd | Fluorescent observation device |
US6148227A (en) | 1998-01-07 | 2000-11-14 | Richard Wolf Gmbh | Diagnosis apparatus for the picture providing recording of fluorescing biological tissue regions |
WO2000042910A1 (en) | 1999-01-26 | 2000-07-27 | Newton Laboratories, Inc. | Autofluorescence imaging system for endoscopy |
Non-Patent Citations (3)
Title |
---|
Alfano et al., "Fluroescence spectra from cancerous and normal human breast and lung tissues", IEEE Journal of Quantam Electronics, vol. QE-23, No. 10, pp. 1806-1811, 1987. |
Andersson-Engels et al., "Tissue diagnostics using laser induced fluorescence", Ber. Bunsenges, Physical Chemistry, No. 93, pp. 335-342, 1989. |
Hung et al., "Autofluorescence of normal and malignant bronchial tissue", Lasers in Surgery and Medicine, No. 11, pp. 99-105, 1991. |
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US20040196463A1 (en) * | 1999-12-22 | 2004-10-07 | Xillix Technologies Corporation | Portable system for detecting skin abnormalities based on characteristic autofluorescence |
US20100198010A1 (en) * | 2000-07-14 | 2010-08-05 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
US9968244B2 (en) | 2000-07-14 | 2018-05-15 | Novadaq Technologies ULC | Compact fluorescence endoscopy video system |
US7341557B2 (en) | 2000-07-14 | 2008-03-11 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
US20020035330A1 (en) * | 2000-07-14 | 2002-03-21 | Xillix Technologies Corporation | Compact fluorescent endoscopy video system |
US20100210904A1 (en) * | 2000-07-14 | 2010-08-19 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
US6821245B2 (en) | 2000-07-14 | 2004-11-23 | Xillix Technologies Corporation | Compact fluorescence endoscopy video system |
US20050065406A1 (en) * | 2000-07-14 | 2005-03-24 | Xillix Technologies Corporation | Compact fluorescence endoscopy video system |
US7722534B2 (en) | 2000-07-14 | 2010-05-25 | Novadaq Technologies, Inc. | Compact fluorescence endoscopy video system |
US8961403B2 (en) | 2000-07-14 | 2015-02-24 | Novadaq Technologies Inc. | Compact fluorescence endoscopy video system |
US20030158470A1 (en) * | 2000-09-18 | 2003-08-21 | Sti Medical Systems, Inc. | Dual mode real-time screening and rapid full-area, selective-spectral, remote imaging and analysis device and process |
US6678398B2 (en) * | 2000-09-18 | 2004-01-13 | Sti Medical Systems, Inc. | Dual mode real-time screening and rapid full-area, selective-spectral, remote imaging and analysis device and process |
US8825140B2 (en) | 2001-05-17 | 2014-09-02 | Xenogen Corporation | Imaging system |
US20030045799A1 (en) * | 2001-07-09 | 2003-03-06 | L'oreal | Device, system and method for observing a typological characteristic of the body |
US7986987B2 (en) * | 2001-07-09 | 2011-07-26 | L' Oréal | Device, system and method for observing a typological characteristic of the body |
US7738032B2 (en) | 2001-11-08 | 2010-06-15 | Johnson & Johnson Consumer Companies, Inc. | Apparatus for and method of taking and viewing images of the skin |
US20050143627A1 (en) * | 2002-01-15 | 2005-06-30 | Xillix Technologies Corporation | Fluorescence endoscopy video systems with no moving parts in the camera |
US10182709B2 (en) | 2002-01-15 | 2019-01-22 | Novadaq Technologies ULC | Filter for use with imaging endoscopes |
US6899675B2 (en) | 2002-01-15 | 2005-05-31 | Xillix Technologies Corp. | Fluorescence endoscopy video systems with no moving parts in the camera |
US20060241496A1 (en) * | 2002-01-15 | 2006-10-26 | Xillix Technologies Corp. | Filter for use with imaging endoscopes |
US7397456B2 (en) * | 2003-04-24 | 2008-07-08 | Hitachi Displays, Ltd. | Inspecting method and inspecting device of control signal for display device, and display unit having this inspecting function |
US20040212609A1 (en) * | 2003-04-24 | 2004-10-28 | Yoichi Igarashi | Inspecting method and inspecting device of control signal for display device, and display unit having this inspecting function |
US20100238405A1 (en) * | 2003-10-30 | 2010-09-23 | Welch Allyn, Inc. | Diagnosis of optically identifiable ophthalmic conditions |
US20100014050A1 (en) * | 2003-10-30 | 2010-01-21 | Newman Richard W | Apparatus and method of diagnosis of optically identifiable ophthalmic conditions |
US20150286794A1 (en) * | 2003-10-30 | 2015-10-08 | Welch Allyn, Inc. | Apparatus for health correlation assessment |
US9563742B2 (en) | 2003-10-30 | 2017-02-07 | Welch Allyn, Inc. | Apparatus for diagnosis of optically identifiable ophthalmic conditions |
US20050094099A1 (en) * | 2003-10-30 | 2005-05-05 | Welch Allyn, Inc. | Apparatus and method for diagnosis of optically identifiable ophthalmic conditions |
US8439501B2 (en) | 2003-10-30 | 2013-05-14 | Welch Allyn, Inc. | Diagnosis of optically identifiable ophthalmic conditions |
US7575321B2 (en) | 2003-10-30 | 2009-08-18 | Welch Allyn, Inc. | Apparatus and method of diagnosis of optically identifiable ophthalmic conditions |
US9060728B2 (en) | 2003-10-30 | 2015-06-23 | Welch Allyn, Inc. | Apparatus for health correlation assessment |
US8075136B2 (en) | 2003-10-30 | 2011-12-13 | Welch Allyn, Inc. | Apparatus and method of diagnosis of optically identifiable ophthalmic conditions |
US7708403B2 (en) | 2003-10-30 | 2010-05-04 | Welch Allyn, Inc. | Apparatus and method for diagnosis of optically identifiable ophthalmic conditions |
US8702234B2 (en) | 2003-10-30 | 2014-04-22 | Welch Allyn, Inc. | Diagnosis of optically identifiable ophthalmic conditions |
US20060025658A1 (en) * | 2003-10-30 | 2006-02-02 | Welch Allyn, Inc. | Apparatus and method of diagnosis of optically identifiable ophthalmic conditions |
AU2011242140B2 (en) * | 2004-04-14 | 2012-11-29 | Led Medical Diagnostics, Inc. | Systems and methods for detection of disease including oral scopes and ambient light management systems (ALMS) |
US20060092315A1 (en) * | 2004-10-29 | 2006-05-04 | Johnson & Johnson Consumer Companies, Inc. | Skin Imaging system with probe |
US8026942B2 (en) | 2004-10-29 | 2011-09-27 | Johnson & Johnson Consumer Companies, Inc. | Skin imaging system with probe |
US20060126127A1 (en) * | 2004-12-09 | 2006-06-15 | Stanback John H | System and method for detecting and correcting defective pixels in a digital image sensor |
US7460688B2 (en) * | 2004-12-09 | 2008-12-02 | Aptina Imaging Corporation | System and method for detecting and correcting defective pixels in a digital image sensor |
US20100111387A1 (en) * | 2005-01-19 | 2010-05-06 | Dermaspect, Llc | Devices and methods for identifying and monitoring changes of a suspect area of a patient |
US7657101B2 (en) * | 2005-01-19 | 2010-02-02 | Dermaspect, Llc | Devices and methods for identifying and monitoring changes of a suspect area on a patient |
US20060210132A1 (en) * | 2005-01-19 | 2006-09-21 | Dermaspect, Llc | Devices and methods for identifying and monitoring changes of a suspect area on a patient |
US8068675B2 (en) | 2005-01-19 | 2011-11-29 | Dermaspect, Llc | Devices and methods for identifying and monitoring changes of a suspect area of a patient |
US9723270B2 (en) | 2005-01-19 | 2017-08-01 | Dermaspect Llc | Devices and methods for identifying and monitoring changes of a suspect area of a patient |
US20060264761A1 (en) * | 2005-03-18 | 2006-11-23 | Jochem Knoche | Portable fluorescence scanner for molecular signatures |
US20070015963A1 (en) * | 2005-05-04 | 2007-01-18 | Xillix Technologies Corp. | Filter for use with imaging endoscopes |
US8630698B2 (en) | 2005-05-04 | 2014-01-14 | Novadaq Technologies, Inc. | Filter for use with imaging endoscopes |
US20070004972A1 (en) * | 2005-06-29 | 2007-01-04 | Johnson & Johnson Consumer Companies, Inc. | Handheld device for determining skin age, proliferation status and photodamage level |
US20070002479A1 (en) * | 2005-06-29 | 2007-01-04 | Johnson & Johnson Consumer Companies, Inc. | Apparatus and method for viewing the skin |
US8532736B1 (en) * | 2005-07-29 | 2013-09-10 | Hewlett-Packard Development Company, L.P. | Apparatus and a method for quantifying properties of skin |
US10265419B2 (en) | 2005-09-02 | 2019-04-23 | Novadaq Technologies ULC | Intraoperative determination of nerve location |
US10827970B2 (en) | 2005-10-14 | 2020-11-10 | Aranz Healthcare Limited | Method of monitoring a surface feature and apparatus therefor |
US9955910B2 (en) | 2005-10-14 | 2018-05-01 | Aranz Healthcare Limited | Method of monitoring a surface feature and apparatus therefor |
US9877654B2 (en) | 2006-02-07 | 2018-01-30 | Novadaq Technologies Inc. | Near infrared imaging |
US9386909B2 (en) | 2006-07-28 | 2016-07-12 | Novadaq Technologies Inc. | System and method for deposition and removal of an optical element on an endoscope objective |
US10434190B2 (en) | 2006-09-07 | 2019-10-08 | Novadaq Technologies ULC | Pre-and-intra-operative localization of penile sentinel nodes |
US9079762B2 (en) | 2006-09-22 | 2015-07-14 | Ethicon Endo-Surgery, Inc. | Micro-electromechanical device |
US20080080755A1 (en) * | 2006-10-02 | 2008-04-03 | Gregory Payonk | Apparatus and Method for Measuring Photodamage to Skin |
US20080079843A1 (en) * | 2006-10-02 | 2008-04-03 | Jeffrey Pote | Imaging Apparatus and Methods for Capturing and Analyzing Digital Images of the Skin |
US7558416B2 (en) | 2006-10-02 | 2009-07-07 | Johnson & Johnson Consumer Companies, Inc. | Apparatus and method for measuring photodamage to skin |
US7764303B2 (en) | 2006-10-02 | 2010-07-27 | Johnson & Johnson Consumer Companies, Inc. | Imaging apparatus and methods for capturing and analyzing digital images of the skin |
US10694151B2 (en) | 2006-12-22 | 2020-06-23 | Novadaq Technologies ULC | Imaging system with a single color image sensor for simultaneous fluorescence and color video endoscopy |
US11770503B2 (en) | 2006-12-22 | 2023-09-26 | Stryker European Operations Limited | Imaging systems and methods for displaying fluorescence and visible images |
US10694152B2 (en) | 2006-12-22 | 2020-06-23 | Novadaq Technologies ULC | Imaging systems and methods for displaying fluorescence and visible images |
US7713265B2 (en) | 2006-12-22 | 2010-05-11 | Ethicon Endo-Surgery, Inc. | Apparatus and method for medically treating a tattoo |
US11025867B2 (en) | 2006-12-22 | 2021-06-01 | Stryker European Operations Limited | Imaging systems and methods for displaying fluorescence and visible images |
US8801606B2 (en) | 2007-01-09 | 2014-08-12 | Ethicon Endo-Surgery, Inc. | Method of in vivo monitoring using an imaging system including scanned beam imaging unit |
US8273015B2 (en) | 2007-01-09 | 2012-09-25 | Ethicon Endo-Surgery, Inc. | Methods for imaging the anatomy with an anatomically secured scanner assembly |
EP2122331A4 (en) * | 2007-01-23 | 2013-10-23 | Novadaq Technologies Inc | System for multi- wavelength fluorescence and reflectance imaging |
EP2122331A1 (en) * | 2007-01-23 | 2009-11-25 | Novadaq Technologies Inc. | System for multi- wavelength fluorescence and reflectance imaging |
US20080177140A1 (en) * | 2007-01-23 | 2008-07-24 | Xillix Technologies Corp. | Cameras for fluorescence and reflectance imaging |
US8216214B2 (en) | 2007-03-12 | 2012-07-10 | Ethicon Endo-Surgery, Inc. | Power modulation of a scanning beam for imaging, therapy, and/or diagnosis |
US8626271B2 (en) | 2007-04-13 | 2014-01-07 | Ethicon Endo-Surgery, Inc. | System and method using fluorescence to examine within a patient's anatomy |
US7995045B2 (en) | 2007-04-13 | 2011-08-09 | Ethicon Endo-Surgery, Inc. | Combined SBI and conventional image processor |
US8160678B2 (en) | 2007-06-18 | 2012-04-17 | Ethicon Endo-Surgery, Inc. | Methods and devices for repairing damaged or diseased tissue using a scanning beam assembly |
US7982776B2 (en) | 2007-07-13 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | SBI motion artifact removal apparatus and method |
US9125552B2 (en) | 2007-07-31 | 2015-09-08 | Ethicon Endo-Surgery, Inc. | Optical scanning module and means for attaching the module to medical instruments for introducing the module into the anatomy |
US7983739B2 (en) | 2007-08-27 | 2011-07-19 | Ethicon Endo-Surgery, Inc. | Position tracking and control for a scanning assembly |
US7925333B2 (en) | 2007-08-28 | 2011-04-12 | Ethicon Endo-Surgery, Inc. | Medical device including scanned beam unit with operational control features |
US20090124854A1 (en) * | 2007-11-09 | 2009-05-14 | Fujifilm Corporation | Image capturing device and image capturing system |
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US9610021B2 (en) | 2008-01-25 | 2017-04-04 | Novadaq Technologies Inc. | Method for evaluating blush in myocardial tissue |
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US9642532B2 (en) | 2008-03-18 | 2017-05-09 | Novadaq Technologies Inc. | Imaging system for combined full-color reflectance and near-infrared imaging |
US8050520B2 (en) | 2008-03-27 | 2011-11-01 | Ethicon Endo-Surgery, Inc. | Method for creating a pixel image from sampled data of a scanned beam imager |
US10219742B2 (en) | 2008-04-14 | 2019-03-05 | Novadaq Technologies ULC | Locating and analyzing perforator flaps for plastic and reconstructive surgery |
US20090270717A1 (en) * | 2008-04-25 | 2009-10-29 | Welch Allyn, Inc. | Apparatus and method for diagnosis of optically identifiable ophthalmic conditions |
US8332014B2 (en) | 2008-04-25 | 2012-12-11 | Ethicon Endo-Surgery, Inc. | Scanned beam device and method using same which measures the reflectance of patient tissue |
US10041042B2 (en) | 2008-05-02 | 2018-08-07 | Novadaq Technologies ULC | Methods for production and use of substance-loaded erythrocytes (S-IEs) for observation and treatment of microvascular hemodynamics |
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US11154198B2 (en) | 2008-05-20 | 2021-10-26 | University Health Network | Method and system for imaging and collection of data for diagnostic purposes |
US9042967B2 (en) | 2008-05-20 | 2015-05-26 | University Health Network | Device and method for wound imaging and monitoring |
US11375898B2 (en) | 2008-05-20 | 2022-07-05 | University Health Network | Method and system with spectral filtering and thermal mapping for imaging and collection of data for diagnostic purposes from bacteria |
US11284800B2 (en) | 2008-05-20 | 2022-03-29 | University Health Network | Devices, methods, and systems for fluorescence-based endoscopic imaging and collection of data with optical filters with corresponding discrete spectral bandwidth |
US20100016711A1 (en) * | 2008-07-21 | 2010-01-21 | University Of South Carolina | Membrane-Deformation Mapping Technique |
US8767049B2 (en) * | 2008-07-21 | 2014-07-01 | University Of South Carolina | Membrane-deformation mapping technique |
WO2010011763A1 (en) * | 2008-07-22 | 2010-01-28 | Jaafar Tindi | Handheld apparatus to determine the viability of a biological tissue |
US20110224518A1 (en) * | 2008-07-22 | 2011-09-15 | Jaafar Tindi | Handheld apparatus to determine the viability of a biological tissue |
US20100249545A1 (en) * | 2009-03-24 | 2010-09-30 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US9999385B2 (en) | 2009-03-24 | 2018-06-19 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US11141099B2 (en) | 2009-03-24 | 2021-10-12 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US9844333B2 (en) | 2009-03-24 | 2017-12-19 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US10813582B2 (en) | 2009-03-24 | 2020-10-27 | International Business Machines Corporation | Remote delivery and monitoring of health care |
US10492671B2 (en) | 2009-05-08 | 2019-12-03 | Novadaq Technologies ULC | Near infra red fluorescence imaging for visualization of blood vessels during endoscopic harvest |
US20110054310A1 (en) * | 2009-08-31 | 2011-03-03 | John David Taylor | Portable medical imaging apparatus for documentation of dermatological areas and subjects of interest |
US8606345B2 (en) | 2009-08-31 | 2013-12-10 | Gsm Of Kansas, Inc. | Medical dual lens camera for documentation of dermatological conditions with laser distance measuring |
US20110164249A1 (en) * | 2009-11-04 | 2011-07-07 | Olympus Corporation | Light spectrum detection method |
US9814378B2 (en) | 2011-03-08 | 2017-11-14 | Novadaq Technologies Inc. | Full spectrum LED illuminator having a mechanical enclosure and heatsink |
US8900126B2 (en) | 2011-03-23 | 2014-12-02 | United Sciences, Llc | Optical scanning device |
EP2554107A1 (en) * | 2011-08-05 | 2013-02-06 | GC Corporation | Intraoral inspection apparatus and method for operating intraoral inspection apparatus |
US11850025B2 (en) | 2011-11-28 | 2023-12-26 | Aranz Healthcare Limited | Handheld skin measuring or monitoring device |
US10874302B2 (en) | 2011-11-28 | 2020-12-29 | Aranz Healthcare Limited | Handheld skin measuring or monitoring device |
US10973411B2 (en) | 2012-02-06 | 2021-04-13 | Carl Zeiss Meditec Ag | Method and device for examining a biological tissue by analysing fluorescence response to illumination and for treating the tissue |
US9883804B2 (en) | 2012-02-06 | 2018-02-06 | Carl Zeiss Meditec Ag | Method and device for examining a biological tissue by analysing fluorescence response to illumination and for treating the tissue |
WO2013117330A1 (en) * | 2012-02-06 | 2013-08-15 | Carl Zeiss Meditec Ag | Method and device for examining a biological tissue by analysing fluorescence response to illumination and for treating the tissue |
US8715173B2 (en) * | 2012-03-12 | 2014-05-06 | United Sciences, Llc | Otoscanner with fan and ring laser |
US8900129B2 (en) | 2012-03-12 | 2014-12-02 | United Sciences, Llc | Video otoscanner with line-of-sight probe and screen |
US8900127B2 (en) | 2012-03-12 | 2014-12-02 | United Sciences, Llc | Otoscanner with pressure sensor for compliance measurement |
US8900128B2 (en) | 2012-03-12 | 2014-12-02 | United Sciences, Llc | Otoscanner with camera for video and scanning |
US8900130B2 (en) | 2012-03-12 | 2014-12-02 | United Sciences, Llc | Otoscanner with safety warning system |
US8900125B2 (en) | 2012-03-12 | 2014-12-02 | United Sciences, Llc | Otoscanning with 3D modeling |
US11284801B2 (en) | 2012-06-21 | 2022-03-29 | Stryker European Operations Limited | Quantification and analysis of angiography and perfusion |
US10278585B2 (en) | 2012-06-21 | 2019-05-07 | Novadaq Technologies ULC | Quantification and analysis of angiography and perfusion |
US20160058362A1 (en) * | 2013-04-18 | 2016-03-03 | Koninklijke Philips N.V. | Acquiring cervical images |
US10178971B2 (en) * | 2013-04-18 | 2019-01-15 | Koninklijke Philips N.V. | Acquiring cervical images |
EP2888989A1 (en) | 2013-12-31 | 2015-07-01 | Karl Storz Imaging, Inc. | Switching between white light imaging and excitation light imaging leaving last video frame displayed |
US10602918B2 (en) | 2013-12-31 | 2020-03-31 | Karl Storz Imaging, Inc. | Switching between white light imaging and excitation light imaging leaving last video frame displayed |
US10602917B2 (en) | 2013-12-31 | 2020-03-31 | Karl Storz Imaging, Inc. | Switching between white light imaging and excitation light imaging leaving last video frame displayed |
US10438356B2 (en) | 2014-07-24 | 2019-10-08 | University Health Network | Collection and analysis of data for diagnostic purposes |
US11676276B2 (en) | 2014-07-24 | 2023-06-13 | University Health Network | Collection and analysis of data for diagnostic purposes |
US11954861B2 (en) | 2014-07-24 | 2024-04-09 | University Health Network | Systems, devices, and methods for visualization of tissue and collection and analysis of data regarding same |
US9816930B2 (en) | 2014-09-29 | 2017-11-14 | Novadaq Technologies Inc. | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US10488340B2 (en) | 2014-09-29 | 2019-11-26 | Novadaq Technologies ULC | Imaging a target fluorophore in a biological material in the presence of autofluorescence |
US10631746B2 (en) | 2014-10-09 | 2020-04-28 | Novadaq Technologies ULC | Quantification of absolute blood flow in tissue using fluorescence-mediated photoplethysmography |
US10145738B2 (en) * | 2015-09-01 | 2018-12-04 | Carl Zeiss Meditec Ag | Optical filter system and fluorescence detection system |
US20180180477A1 (en) * | 2015-09-01 | 2018-06-28 | Carl Zeiss Meditec Ag | Optical filter system and fluorescence detection system |
US11930278B2 (en) | 2015-11-13 | 2024-03-12 | Stryker Corporation | Systems and methods for illumination and imaging of a target |
US10980420B2 (en) | 2016-01-26 | 2021-04-20 | Stryker European Operations Limited | Configurable platform |
US11298024B2 (en) | 2016-01-26 | 2022-04-12 | Stryker European Operations Limited | Configurable platform |
US10293122B2 (en) | 2016-03-17 | 2019-05-21 | Novadaq Technologies ULC | Endoluminal introducer with contamination avoidance |
USD916294S1 (en) | 2016-04-28 | 2021-04-13 | Stryker European Operations Limited | Illumination and imaging device |
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US20040196463A1 (en) | 2004-10-07 |
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